Apparatus for modifying the surface of the eye through large beam laser polishing and method of controlling the apparatus

ABSTRACT

A apparatus and method for controlling an apparatus for removing tissue from the eye performs various types of corrections using a relatively large beam, but oscillating, or dithering, that being to prevent reinforcing ridges from being formed during the tissue removal process. Further, various types of correction, such as hyperopia and astigmatism correction, are performed using a large beam that is scanned over the area to be ablated using overlapping shots. Further, the epithelium in the area to be treated is removed using an infrared fluorescent dye to dye the epithelium, and then observing the fluorescent patterns from the epithelium area to be removed. Once a certain area is no longer fluorescent after laser shots, smaller shots are then applied, selectively removing the epithelium from the remaining regions. Again, the fluorescence patterns are observed, and the process is repeated until no epithelium remains. At this point, all of the epithelium is removed, and further a map is created of the initial epithelial thickness at each point in the area from which the epithelium was removed.

This application is a Continuation of U.S. application Ser. No.08/487,281 filed on Jun. 7, 1995, now U.S. Pat. No. 5,827,262, which wasDivisional of U.S. application Ser. No. 08/338,495 filed on Nov. 16,1994, now U.S. Pat. No. 5,683,379, which was the national stage ofPCT/EP93/02667, filed Sep. 30, 1993, all of which are herebyincorporated by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The invention relates to an apparatus for surgically modifying thecurvature of the eye cornea and a method of controlling the apparatus,and more particularly to an apparatus for smoothly correcting a varietyof corneal defects and a method of controlling the apparatus.

2. Description of the Related Art

Since the initial development of corrective lenses, new and better waysof correcting defective eyesight have been developed. From the bifocallens and extended wear soft contact lens to corneal incisions andshaping, the field of ophthalmology has seen great advances inconvenience, safety, and accuracy in correcting a variety of sightdefects, including myopia, hyperopia, and astigmatism.

While corrective lenses still find wide general application,ophthalmologists are focussing on surgery to correct such defects. Oneof the most popular surgical techniques is radial keratotomy, in which asurgeon forms radial slits in the outer surface of the cornea, allowingthe cornea to re-shape and resulting in a modified cornea to correct thedeficiencies of the patient's sight. This technique has continued todevelop, but the advent of the laser and its introduction into the fieldof medicine have given rise to a new and potentially revolutionarymethod of eye surgery. Specifically, the development of the excimerlaser and its application to eye surgery has opened a new approach toophthalmological surgery.

The excimer laser produces coherent light of a very short wavelength ofaround 193 nm. At these wavelengths and the resulting high energies, theexcimer laser removes, or ablates, tissue at the molecular level withoutsignificant heating of adjacent tissue. Thus, rather than “burning” awaytissue, the excimer laser literally breaks the molecular bonds, and theablated tissue is ejected from the ablated surface leaving a relativelyunmarred surface to heal virtually scar-free. This aspect of the excimerlaser is now well known and is further described, for example, in U.S.Pat. No. 4,784,135 entitled “Far Ultraviolet Surgical and DentalProcedures,” issued Nov. 15, 1988.

The word “excimer” in excimer laser was initially drawn from itsmolecular principal of operation. The excimer laser was initially basedon the lasing action of excited dimers, such as xenon, krypton, orfluorine in the form of Xe₂, Kr₂, or F₂. The word “excimer” as appliedto lasers is now a misnomer, as the most popular excimer laser used ineye surgery does not even use dimers—it uses argon fluoride. The excimerlaser is also a pumped laser, in the sense that another laser is used tostimulate the lasing action of the argon fluoride mixture in the lasercavity. “Eximer laser” has now come to be applied to an entire group oflasers with ultraviolet wavelengths below 400 nm.

When used in ophthalmological surgery, the eximer laser is preferablypulsed, as that allows for application of high energies without thermalheating. These pulses are very short bursts of high energy laser lightapplied to the cornea. For example, such a laser is typically pulsed atbetween 1 to 50 Hz with a 10 to 20 ns pulse duration. A drawback of theeximer laser, however, is the energy density over the beam tends to haveboth large and small scale inhomogeneities. The application of theexcimer laser for surgical procedures is described in U.S. Pat. No.4,784,135, entitled “Far Ultraviolet Surgical and Dental Procedures,”issued Nov. 15, 1988. For a historical background of the development andapplication of the eximer laser to ophthalmic surgery, see Chapter 1 ofthe Color Atlas/Text of Excimer Laser Surgery, ©1993 Igaku-Shoin MedicalPublishers, Inc.

As early as 1983, researchers recognized the potential application ofexcimer laser light in reshaping the cornea. Since that time, a numberof systems have been developed to reshape the cornea, using a variety oftechniques such as variable sized circular apertures to correct formyopia, variable sized ring shaped apertures to correct for hyperopia,and variable sized slit shaped apertures to correct for astigmatism.These techniques collectively came to be known as photorefractivekeratectomy. It has been recognized that using such apertures to correctfor myopia, for example, a series of excimer laser shots usingprogressively smaller spot sizes could ablate away a portion of thecornea to effectively build a “corrective lens” into the cornea. Thesetechniques are discussed, for example, in U.S. Pat. No. 4,973,330,entitled “Surgical Apparatus for Modifying the Curvature of the EyeCornea,” issued Nov. 27, 1990, and in U.S. Pat. No. 4,729,372, entitled“Apparatus for Performing Ophthalmic Laser Surgery,” issued Mar. 8,1988. Those skilled in the art of laser ophthalmological surgery haveextensively developed the required exposure patterns using thesevariable size apertures to provide an appropriate amount of correctionto various degrees of myopia, hyperopia, and astigmatism, and acombination of these conditions.

These multiple aperture systems, however, suffer a number of drawbacks.They tend to be complicated and inflexible, requiring a number ofaperture wheels or masks and only providing standard forms of correctionfor myopia and hyperopia with circular symmetry and astigmatism withcylindrical symmetry. The human eye, however, tends to have more subtledefects. A system that could accommodate these defects and provide moreadaptable solutions, as well as a physically simpler components, wouldthus be advantageous.

An apparatus for ablating tissue from the eye is shown in U.S. Pat. No.4,973,330, referenced above. This apparatus includes an excimer laser,the laser beam of which impinges on the cornea, with the axis of thelaser beam coinciding with the optical axis of the eye. Furthermore, afield stop limits the area of the laser spot on the cornea illuminatedby the laser beam, and the size of this field stop is set in atemporarily variable manner according to the profile of the area to beremoved so that the thickness of the area to be removed is a function ofthe distance from the optical axis of the eye.

The system described in U.S. Pat. No. 4,973,330 permits in this waysetting the “laser energy deposited” on the cornea as the function ofthe distance from the optical axis of the eye, but only under thecondition that the distribution of energy (i.e., the power of the laserbeam spot) is homogeneous, or at least axially symmetrical. This,however, is a condition that excimer lasers in particular do not alwaysfulfill. Inhomogeneous power distribution results in non-axiallysymmetrical removal. Moreover, the system described in U.S. Pat. No.4,973,330 only permits the correction of spherical aberrations, notastigmatism.

An apparatus based on the same fundamental idea is known from U.S. Pat.No. 4,994,058, entitled “Surface Shaping Using Lasers”, issued Feb. 19,1991. That apparatus employs a “destructible field stop mask” instead ofa field stop having a temporarily variable aperture.

Another class of apparatus for shaping the cornea by means of removingtissue is known from the various L'Esperance patents. These include U.S.Pat. No. 4,665,913, entitled “Method for Ophthalmological Surgery,”issued May 19, 1987; U.S. Pat. No. 4,669,466, entitled “Method andApparatus for Analysis and Correction of Abnormal Refractive Errors ofthe Eye,” issued Jun. 2, 1987; U.S. Pat. No. 4,718,418, entitled“Apparatus for Ophthalmological surgery,” issued Jan. 12, 1988; U.S.Pat. No. 4,721,379, entitled “Apparatus for Analysis and Correction ofAbnormal Refractive Errors of the Eye,” issued Jan. 26, 1988; U.S. Pat.No. 4,729,372, entitled “Apparatus for Performing Ophthalmic LaserSurgery,” issued Mar. 8, 1988; U.S. Pat. No. 4,732,148, entitled “Methodfor Performing Ophthalmic Laser Surgery,” issued Mar. 22, 1988; U.S.Pat. No. 4,770,172, entitled “Method of Laser-Sculpture of the Opticallyused Portion of the Cornea,” issued Sep. 13, 1988; U.S. Pat. No.4,773,414, entitled “Method of Laser-Sculpture of the optically usedPortion of the Cornea,” issued Sep. 27, 1988; and U.S. Pat. No.4,798,204, entitled “Method of Laser-Sculpture of the Optically usedPortion of the Cornea,” issued Jan. 17, 1989. In that apparatus, a laserbeam with a small focus spot is moved by a two-dimensional scanningsystem over the area to be removed. This apparatus, which operates as a“scanner,” has the advantage that it can generate any two-dimensionalprofile of deposited energy “over the area to be removed.” Because ofthe small size of the beam spot, the period of treatment, however, isvery great, as power per area unit cannot be raised above a specific“critical” value.

Thus, current techniques do not adequately address the non-linear energydistribution of an excimer laser. The excimer laser includes both largescale and small scale non-linearities in its energy distribution. Thiscan cause over-ablation and under-ablation of certain areas of the eyeunder treatment. Thus it would be desirable to provide a system thatfurther homogenizes the effective energy deposited on the eye.

Systems that use apertures to create a series of progressively smallershot sizes also suffer from the disadvantage of creating sharp ridges inthe treatment zone of the cornea. Especially near the periphery of thetreatment zone, a number of shots are typically required to create thenecessary ablation depth at each particular spot size. The typicalablation depth for each shot is 0.2 μm. When multiple shots are requiredat a single aperture size, the ridge depth reinforces, creating aneffective ridge of some multiple of 0.2 μm. For example, five shotswould result in a ridge height of 1.0 μm. These sharp ridges in thetreatment zone can lead to unwanted epithelial regrowth, especially whencorrecting high diopter defects. A system that minimizes such ridgeswould promote smoother epithelial healing, preventing excessive regrowthand allowing the corrected eye to retain its correction for a longerperiod of time and with more stability.

Before ablating, most current excimer techniques also require physicallyscraping away the epithelial layer from the eye. This can be a traumaticprocedure for the patient, and requires a high degree of precision bythe surgeon. Alternative, less invasive methods of removal of theepithelium before ablation of the cornea are thus desirable.

SUMMARY OF THE INVENTION

The method and apparatus according to the invention provides cornealcorrection using laser “polishing” or “dithering” in which subsequentshots used to ablate the eye are randomly or otherwise moved from acenter axis of treatment to prevent the formation of large ridges in thetreatment zone.

Further according to the invention, instead of using various apertureshapes, a relatively large beam is moved along the line of hyperopic orastigmatic correction desired, creating a line of overlapping shots. Iffurther correction is necessary, overlapping lines are then createdusing various beam sizes, thus forming the desired correction curve inthe cornea.

Further according to the invention, using this scanning beam technique,various non-symmetrical optical defects are corrected, such as a“curved” astigmatism, by modifying the line of travel of the overlappingshots or by otherwise generating a sequence of shots to appropriatelyablate a non-symmetrical defect.

Further in the system and method according to the invention, theepithelium is removed using laser ablation. The epithelium is first dyedwith an infrared fluorescent dye. The epithelium is then continuallyablated using a beam covering the area of epithelium to be removed untilan infrared scanning device recognizes that some portion of theepithelium is gone, as indicated by a lack of fluorescence. Then, eithermanually or under computer control, the spot size is reduced and areasthat still fluoresce are ablated until they no longer fluoresce. This isrepeated until the epithelium has been removed from the entire treatmentarea. This technique can also map the initial thickness of theepithelium before removal.

BRIEF DESCRIPTION OF THE DRAWINGS

A better understanding of the present invention can be obtained when thefollowing detailed description of the preferred embodiment is consideredin conjunction with the following drawings, in which:

FIG. 1A is a simplified diagram illustrating a typical excimer laser eyesurgery system in which can be implemented the apparatus and methodaccording to the invention;

FIG. 1B is a more detailed diagram illustrating the system of FIG. 1A;

FIG. 2A is a view along the center axis of the treatment zoneillustrating a typical large beam ablation pattern to correct formyopia;

FIG. 2B is a side profile of FIG. 2A, further illustrating the use oftransition zones;

FIG. 3A is a view along the center axis of the treatment zoneillustrating random dithering according to the invention;

FIG. 3B is a view along the center axis of the treatment zoneillustrating circular dithering according to the invention;

FIGS. 4A and 4B are illustrations showing a shot pattern for astigmaticcorrection according to the invention;

FIG. 5 is an illustration of a treatment zone illustrating a shottreatment pattern for a curved astigmatism according to the invention;

FIGS. 6A and 6B are illustrations showing a shot pattern for treatmentof hyperopia according to the invention;

FIGS. 7A and 7B are side profiles of the cornea illustrating initial andending radii of curvature over a treatment zone for correction of myopiaand hyperopia;

FIG. 8 is an illustration of shot patterns used to correct for generalnon-symmetrical aberrations of the eye according to the invention;

FIG. 9 is a flowchart illustrating a calculation routine used to performcorrection for astigmatism, hyperopia, and myopia using the random orcircular dithering and large beam scanning according to the invention;

FIGS. 10 and 11 are flowcharts illustrating an astigmatism routine usedby the calculation routine of FIG. 9;

FIG. 12 is a flowchart illustrating a hyperopia routine used by thecalculation routine of FIG. 9;

FIG. 13 is a flowchart of a random dithering routine used by thecalculation routine of FIG. 9;

FIG. 14 is a flowchart of a circular dithering routine used by thecalculation routine of FIG. 9; and

FIGS. 15 and 16 are views along the axis of treatment of the eyeillustrating ablation of the epithelium according to the invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

FIG. 1A, according to the invention, shows an excimer laser 20 providinga beam to a beam homogenizer 24 that also includes focusing components.The beam homogenizer 24 then provides a relatively homogeneous beam 22to a field stop in the form of a diaphragm 36, which is regulated by acontrol unit 64 in such a manner that it limits the laser spot on an eye44 to an area the maximum size of which is between approximately 10% andapproximately 90% of the area of the region in which the tissue is to beremoved when ablation is performed to correct for astigmatism orhyperopia. This preferred maximum size is more dependent on the shapeand size of the area to be ablated rather than any fixed percentage, andcould be, for example, between 20% and 80%. The larger the size of thespot that can be used the better, as that reduces treatment time.

Moreover, a beam manipulator unit in the form of a scanning mirror 42 isprovided that also is regulated by the control unit 64. The scanningmirror 42 moves the axis of the beam 22 over at least a part of theregion on the eye 44 in which the tissue is to be removed.

The invention thus provides an eye surgery system 10 for shaping thecornea by removing tissue with which removal of non-axially symmetricalprofiles can be realized in a relatively shorter time. Further, the eyesurgery system 10 compensates for any inhomogeneous distribution ofenergy over the beam spot.

By this means, not only can a very small spot be illuminated, as in thecase of a scanning unit, but also a relatively large region can beilluminated so that the treatment can occur relatively quickly. Toshorten treatment time, it is preferred to maintain the size of thelaser spot on the eye 44 as large as possible for as long as possible,for example to at least 50% of the size of the region to be treated.

The scanning mirror 42 can, by way of illustration, tilt about or aroundat least one axis. Mirror elements that can be used, and in particularthat can be tilted about two axes, are described in U.S. Pat. No.4,175,832, for example.

Further, the control unit 64 can regulate the size of the laser spot onthe eye 44 in correlation to the movement of the beam axis (through useof the scanning mirror 42) on the eye 44, thus precisely regulating theenergy deposited on a specific area of the eye 44. Thus, non-axiallysymmetrical profiles can be generated on the corneal surface of the eye44. Different types of diaphragms 36 can be used, for example ovals orcircles with blocked centers.

Moreover, the scanning mirror 42 can be placed in the beam 22 not onlyafter the diaphragm 36, but also before the diaphragm 36. It would thenbe preferable to move the diaphragm 36 synchronously with the scanningmirror 42.

In correcting spherical aberrations, the control unit 64 preferablymoves the scanning mirror 42 such that the beam 22 oscillates from shotto shot in at least one direction, such as is illustrated by an arrow12. Such oscillation compensates for inhomogeneity of the energydistribution over the beam 22. This oscillation finds applicationregardless of the maximum beam size.

To correct astigmatism, the scanning mirror 42 moves the axis of thebeam 22 between at least two directions, neither of which are collinearwith the axis of treatment of the eye 44. This permits treating anastigmatic eye, which, without being limited by theory, the latestresearch states has not one apex, but two. That is, it has the shape ofcamel humps. Also, the control unit 64 regulates the scanning mirror 42such that the axis of the beam 22 oscillates at least one-dimensionallyabout each direction, thus compensating for homogeneity of the beam 22.

To correct for hyperopia, the axis of the beam 22 is preferably moved ona conic-shaped shell surface, it also being possible to superimpose anat least one-dimensional oscillation to compensate for inhomogeneity ofthe beam 22. By moving on a conic-shaped shell surface, a circularpattern of overlapping shots is projected onto the eye 44.

In adapting the diaphragm 36 to the typical shape of the cross-sectionof excimer laser beams, the diaphragm 36 may also have a non-axiallysymmetrical shape, with the diaphragm 36 being turned in order tohomogenize the deposited energy during the movement of the axis of thebeam 22 on the conic shell. The homogenization is enhanced if theturning of the diaphragm 36 occurs asynchronously to the rotation of theaxis of the beam 22 on the conic shell.

FIG. 1B shows additional details of the typical eye surgery system 10 inwhich the method and apparatus according to the invention would beimplemented. An excimer laser 20 provides a pulsed beam 22 to a beamhomogenizer 24 after reflection from optics 26. A shutter 28 is alsoprovided to block transmission of the pulsed beam 22 to the beamhomogenizer 24. The excimer laser 20 is a typical excimer laser as iswell known in the art. It preferably provides a 193 nm wavelength beamwith a maximum pulse energy of 400 mJ/pulse. The excimer laser 20preferably provides maximum power at the treatment site of 1 W, with apulse frequency of 10 Hz and a pulse length of 18 ns. Of course avariety of other excimer lasers could be used, and the apparatus andmethod according to the invention further have application where a laserother than an excimer laser is used. By way of example, the wavelengthof the light from the laser is preferably less than 400 nm, as thatprovides the desired ablating action with reduced thermal heating.Further, other pulse energies can be provided, such as all the way downto 200 mJ/pulse, with typical repetition rates of 60 to 100 pulses persecond with a typical pulse length of 10 to 30 ns. Again, all of theseare merely typical values, and deviation from them can be made withoutchanging the spirit of the apparatus and method according to theinvention. Further examples of such laser systems can be found in U.S.Pat. No. 4,665,913, entitled “Method for Ophthalmological Surgery,”issued May 19, 1987, and U.S. Pat. No. 4,729,372, entitled “Apparatusfor Performing Ophthalmic Laser Surgery,” issued Mar. 8, 1988.

The beam homogenizer 24 preferably includes standard homogenization andfocusing hardware, which can be based both on optical mixing of the beamand on rotation of the beam. For an example of typical beamhomogenization hardware, see U.S. Pat. No. 4,911,711 entitled,“Sculpture Apparatus For Correcting Curvature Of The Cornea,” issuedMar. 27, 1990. Note that by providing the “dithering” according to theinvention as discussed below, the beam homogenizer 24 can be simplerthan the beam homogenization hardware shown in that reference. From thebeam homogenizer 24, the pulsed beam 22 is then reflected off of optics30, which also passes a red pilot laser beam from a pilot laser 32. Thispilot laser 32 is preferably a 633 nm helium neon laser of less than 1mW of power. The red pilot beam from the pilot laser 32 can also beblocked by a shutter 34. The pilot laser 32 is aligned so that itsoptical pathway coincides with the pulsed beam 22. The pilot laser 32provides the functions of centering the beam 22 on the axis of treatmentof the eye 44, and also provides for focusing on the eye 44, as isdiscussed below. Further, it can provide an optical fixation point forthe patient, although a different laser or light source could also beprovided for that purpose.

From the optics 30, the pulsed beam 20 (now also co-aligned with thebeam from the pilot laser 32) then passes through an adjustablediaphragm 36, which allows the beam size to be adjusted before it entersthe final optics. After the diaphragm 36, a spot mode lens 38, when inplace, provides further concentration of the beam 22, allowing spotablation of certain defects in the eye by a physician performingtherapeutic rather than refractive surgery. The spot mode lens 38 isthus moved into and out of place depending on whether therapeutic orrefractive treatment is desired.

Following the spot mode lens 38, a focusing lens 40 directs the beam 22onto the scanning mirror 42, which then reflects the beam 22 onto apatient's eye 44. Note that the portion of the beam 22 from the pilotlaser 32 is used for both adjusting the distance of the eye 44 from theentire eye surgery system 10 and for providing centering, as will bediscussed below. The focusing lens 40 focuses light such that when theeye 44 is at the optimal distance, the beam 22 is properly focused ontothe eye 44.

These various lenses and mirrors thus combine to form an optical systemproviding an excimer beam to the cornea. The optical system creates alaser spot on the cornea, and the spot size is adjustable, along withits location. It will be readily appreciated that a wide variety ofdifferent systems could be used to optically provide such a beam. Forexample, a lens could be used to adjust the spot size rather than anaperture, and instead of a scanning mirror, the patient or the patient'seye 44 could be physically moved to provide for shots at differentlocations on the eye 44.

Also provided in the system according to the invention is a focusinglaser 46, whose beam can also be blocked by a shutter 48. The focusinglaser 46 is preferably a green helium neon laser providing a beam of awavelength of 535 nm and less than 1 mW of power. The beam from thefocusing laser 46 travels through optics 50 and impinges on the eye 44at an angle. The distance of the eye 44 from the eye surgery system 10is adjusted such that both the beam from the pilot laser 32 and the beamfrom the focusing laser 46 impinge on the surface of the eye 44 at thesame point.

Further provided is an optional fixation mask 52, which is well known inthe art and is used to stabilize the eye 44 during surgery. It caninclude debris removal components, and is typically attached to the eye44 through either a vacuum suction ring or through hooks. A clean gaspurge unit 54 ensures that the optics and the beams in the system arefree from any floating debris.

A microscope 56 is provided for the physician to observe progress duringablation of the surface of the eye 44. The microscope 56 is preferably aZEISS OPMI “PLUS” part No. 3033119910, with magnifications of 3.4, 5.6and 9.0 times. Field illumination is provided by a cold light source notshown, which is preferably the Schott KL1500 Electronic, ZEISS partnumber 417075. This microscope 56 focuses through the scanning mirror 42and also focuses through a splitting mirror 58. The splitting mirrorfurther provides a view of the eye 44 to an infrared video unit 60,which is used for the epithelial ablation discussed below. The infraredvideo unit 60 preferably provides an image output to a capturing videoscreen 62 and to a control unit 64. The infrared video unit 60 ispreferably sensitive to both infrared light and visible light.

The control unit 64, which is typically a high performance computercompatible with an IBM PC by International Business Machines Corp.,further preferably controls all components of the eye surgery system 10,including the shutters 28, 34, and 48, the diaphragm 36, the spot modelens 38, and the scanning mirror 42.

FIG. 2A shows a simplified top view of the cornea of a typical eye 44 onwhich myopic correction has been performed. A treatment zone 100 of awidth S is centered on an axis of treatment 102, which does notnecessarily correspond to the optical axis of the eye 44. The treatmentzone 100 is bounded by a first outer ablation ring 104, with subsequentablation rings 106 to 114 shown spaced more widely towards the center ofthe axis of treatment 102 (note that preferably the smaller shots areperformed first).

This wider spacing is topographical in effect, as in a typical system,the change in spot radius between shots may actually be constant, butwith a greater number of shots performed toward the periphery of thetreatment zone 100. Although only six ablation zones are shown, in atypical ablation pattern a greater number of spot sizes are used, and agreater number of shots are also performed. The ablation function forcalculating the necessary depth of ablation for myopia is discussedbelow in conjunction with FIG. 7A.

In performing high dioptric correction for myopia, using the standardablation function discussed below may result in an excessive depth ofablation along the axis of treatment 102. As illustrated in FIG. 2B, thestandard equation for myopic ablation would result, for example, in acurve 120 which would lead to a high depth of ablation along the axis oftreatment 102, and would also result in sharp edges 122 at the corner ofthe treatment zone 100. For simplicity, FIG. 2B shows the effect oftreatment on a flat surface rather than the surface of the cornea. Forsuch a high degree of correction, the use of transition zones cansignificantly reduce the edge effects in healing and can also reduce thecenter depth of ablation along the axis of treatment 102. Thesetransition zones 124 and 126 effectively create a multi-focal lens. InFIG. 2B, two transition zones 124 and 126 are shown resulting in ashallower ablation curve 128. The first of these transition zones 124 iscreated by performing a myopic ablation over the full width S of thetreatment zone 100 using a lesser degree of correction than the ultimatecorrection desired. Only those shots of a radius falling into the radiusof the transition zone 124 are performed, however, thus leaving auniformly ablated surface inside transition zone 124 for furthertreatment. This results in an initial curve 130.

Then, another series of myopic ablation shots using the myopic ablationfunction discussed below is performed using a somewhat greater degree ofcorrection but using a smaller “treatment zone” (in actual practice, thesmaller shots are preferably performed first). This resulting curve anduniformly ablated area 132 creates the second transition zone 126.Finally, a series of shots are performed for the full desired correctionbut using an again narrower zone of treatment, resulting in the finalcurve 134. The use of transition zones is known to the art ofphotorefractive keratectomy, and is described, for example, in Chapter 6of the Color Atlas/Text of Excimer Laser Surgery, © 1993 Igaku-ShoinMedical Publishers, Inc. These transition zones 124 and 126 reduce anysharp edges 122 from being created, which could otherwise result inundesirable patterns of epithelia regrowth, and also reduce ultimatedepth of ablation along the axis of treatment 102.

The following are two typical tables showing transition zones. Fortreatment to correct −9.00 diopters of myopia over a 5 mm treatment zone100, the following transition zones could be used:

Min.  Max. Correction No. [mm] [mm] [diopters] 1 0.50-4.00 −9.00 24.00-4.20 −7.50 3 4.20-4.40 −6.00 4 4.40-4.60 −4.50 5 4.60-4.80 −3.00 64.80-5.00 −1.50

Using this table, first a standard myopic correction using the equationdiscussed below would be performed for the desired −9.00 diopters ofcorrection, but instead over a treatment zone 4.00 mm wide. Thisprovides full correction in the middle 4.00 mm zone. Then, a transitionis created by ablating from 4.00 to 4.20 mm using the lesser correctionof −7.50 diopters. This is repeated for the subsequent entries in thetable, thus forming transition zones of a greater radius of curvature.

Without the transition zones, 88 μm would be ablated at the axis oftreatment 102; with the transition zones, only 71 μm is ablated—20%less. This is good for the stability of the cornea.

An example of treatment for −12.00 diopters over a full 7 mm treatmentzone 100 is illustrated below:

Min.  Max. Correction No. [mm] [mm] [diopters] 1 0.50-2.00 −12.00 22.00-2.20 −11.54 3 2.20-2.40 −11.08 4 2.40-2.60 −10.62 5 2.60-2.80−10.15 6 2.80-3.00 −9.69 7 3.00-3.20 −9.23 8 3.20-3.40 −8.77 9 3.40-3.60−8.31 10 3.60-3.80 −7.85 11 3.80-4.00 −7.38 12 4.00-4.20 −6.92 134.20-4.40 −6.46 14 4.40-4.60 −6.00 15 4.60-4.80 −5.54 16 4.80-5.00 −5.0817 5.00-5.20 −4.62 18 5.20-5.40 −4.15 19 5.40-5.60 −3.69 20 5.60-5.80−3.23 21 5.80-6.00 −2.77 22 6.00-6.20 −2.31 23 6.20-6.40 −1.85 246.40-6.60 −1.38 25 6.60-6.80 −0.92 26 6.80-7.00 −0.46

FIGS. 3A and 3B show an ablation pattern corresponding to one of theablation rings 104 to 114 of FIG. 2A, but using the laser “dithering,”or “polishing,” according to the invention. The term “dithering” is usedin the sense that small random or pseudo random fluctuations are addedto the beam 22 to “smooth” particular errors that would otherwise buildup. Assuming one of the ablation rings 104 to 114 of FIG. 2A includesfive shots at a particular spot size, FIGS. 3A and 3B show the effectachieved according to the method and apparatus of the invention. In FIG.3A, the axis of treatment 102 is shown, upon which shots in past systemshave been centered, as shown in FIG. 2A.

According to the invention, however, the centers of the five shots arerandomly distributed in a dithering zone 140 with the center axis ofeach shot being away from the axis of treatment 102. Five shots usingrandomly distributed centers 142 through 150 result in five individualexcimer laser ablation shots 152 through 160. The radius of thedithering zone 140 is preferably somewhat less than the radius of theshots themselves. As can be seen, any reinforcement—i.e., ridge heightgreater than a single shot ridge height—occurs only incidentally, andgenerally the ridges are distributed over a dithering band 162. Thisprovides a “smoothing” effect, reducing average ridge height.

FIG. 3B shows an alternative manner of performing this polishing, inwhich the shot centers 142 through 150 are evenly distributed around theperiphery of the dithering zone 140. This case insures that none of theablation shots 152 through 160, even though of the same radius, formreinforcing ridges.

In this manner, a smoother surface of the eye 44 is achieved duringablation to correct for myopia. This polishing, or dithering, could alsobe described as an “oscillation” of the laser spot upon the cornea. Thisdithering could also be one dimensional rather than two, and could alsobe created by vibrating the patient's eye 44, such as by vibrating themask 52 or the patient himself. For example, a small mechanical vibratorcould be placed in a patient table or in the mask 52. This could thenprovide the oscillation necessary. As can be readily appreciated, such adithering technique can be applied to other forms of correction, such asusing ring apertures and slit apertures to correct for hyperopia andastigmatism, as are known in the art. Further, the dithering could beapplied to any other shot patterns such as for hyperopia andastigmatism, thus reducing the effects of both ridge height and beam 22inhomogeneity.

FIG. 4 illustrates a large beam scanning pattern used to correct forastigmatism according to the system and method of the invention. In theprior art, variable size slits were generally used to perform thiscorrection, requiring further hardware and generally inflexible patternsof correction.

The method and apparatus according to the invention, however, correctastigmatism within the treatment zone 100, here with width S and lengthL, through a series of lines 170 and 172 created by a series ofoverlapping shots in the area to be corrected for astigmatism. In thediagram, only the first line 170 and the second line 172 are shown, withthe first line created using smaller spot sizes than the second line172. According to the method of the invention, a lesser or greaternumber of lines are used to provide the desired degree of correction forastigmatism. This results in the ablation profile as shown in FIG. 4B.This profile generally corresponds to the curvature needed for a myopiaablation, whose formula is discussed below in conjunction with FIG. 7A.

A typical pattern used for ablating to correct for astigmatism for a−2.00 diopter correction would involve shots of:

No. Spot Size Shots 1 1.067 11 2 1.679 8 3 2.141 7 4 2.484 7 5 2.726 6 62.885 6 7 2.977 6 8 3.019 6 9 3.022 6 10 3.000 6

At each spot size, a line is created corresponding to the lines 102 and104, and preferably the spots overlap by approximately 88%. This wouldcreate an appropriate modified curvature corresponding to a −2.00diopter correction for astigmatism. These would be spread over a 3 mmwidth S of the treatment zone 100.

FIG. 5 is an illustration of shot patterns used to correct fornon-symmetrical astigmatism. In this case, only a single treatment line174 is shown; typically, a greater number of lines would be used, butfor clarity, the single line 174 illustrates the treatment of a curvedastigmatism that does not extend linearly across an axis of treatment102 of the eye 44. In this way, a greater variety of types ofastigmatism are correctable.

FIG. 6A illustrates the large beam scanning according to the inventionused to correct for hyperopia without using ring apertures. Instead,only the single diaphragm 36 is used to adjust the spot size, and acircular ablation ring 180 over the treatment zone 100, as is well knownto those skilled in performing hyperopic ablation, is created usingmultiple rings of different spot sizes and various overlaps. Theapproximate ablation profile is shown in FIG. 6B. The formula for thecurvature for hyperopic ablation is discussed below in conjunction withFIG. 7B.

It will be noted that the shots for hyperopic ablation extend beyond thezone of treatment 100 of width S. The shots outside of this area do notprovide for optical correction, but instead provide a smooth transitionat the edge of hyperopic ablation. Further, although the circularablation ring 180 is not shown extending all the way to the center ofthe axis of treatment 102, the final series of shots at the largest shotsize preferably extend very close to that axis, to provide a smoothprofile from the center of the axis of treatment 102 to the edge of thetreatment zone 100.

A typical shot pattern for hyperopic correction of 5.00 diopters wouldinvolve shots of:

No. Spot Size Shots Overlap 1 2.000 1052 99.25[%] 2 2.469 128 95 3 3.060104 95 4 3.966 80 95 5 4.600 27 87

In this pattern, each series of shots is used to create a ring withcenters at a radius of 2.5 mm from the axis of treatment 102 of the eye44. In this case, the preferred overlap is variable per treatment ring,and is illustrated in the table.

As can further be appreciated, although the illustrated shot patternsuse circular apertures, another aperture shape could be used to createthe hyperopic correction pattern and the astigmatism correction patternaccording to the invention. For example, an oval shot shape could beused, and that oval could be rotated during the hyperopic correction,such that one axis of the oval pointed to the axis of treatment 102 ofthe eye 44. Alternatively, the oval could be rotated asynchronously withthe rotation about the axis of treatment 102, thus further reducing theeffects of inhomogeneity of the beam 22.

FIGS. 7A and 7B illustrate various mathematical attributes of theablation profiles of the preceding ablation patterns. FIG. 7A shows atypical ablation profile for myopic ablation and FIG. 7B illustrates atypical ablation profile for hyperopic ablation. In both, the initialradius of the cornea of the eye 44 is given by R_(OLD) and the new,desired radius of the cornea of the eye 44 is given by R_(NEW). Theabsolute zone of treatment 100 is designated as a width S, whichcorresponds to the effective area that performs the corrective function.It is typically between 2 and 8 mm, but can be larger or smaller. Thedepth of ablation at any point within the treatment zone 100 of width Sis given by a variable A, which stands for ablation depth. The distancefrom the axis of treatment 102 is given by a variable ρ.

To calculate the new radius R_(NEW), the old radius R_(OLD) and adesired dioptric correction D_(CORR) is used in the following equation:${{NEW\_ RADIUS}( {R_{{old}^{\prime}}D_{CORR}} )} = \frac{n - 1}{\frac{n - 1}{R_{OLD}} + D_{CORR}}$

NEW_RADIUS returns a parameter indicating the new radius of correctionneeded, R_(NEW), for a given R_(OLD) and D_(CORR). Both R_(OLD) andR_(NEW) are measured in meters, and are typically between 5 and 15 mm.

The formula for calculating the necessary depth of ablation to correctfor myopia as illustrated in FIG. 7A is given below:${{MYO\_ ABLATE}( {\rho,R_{OLD},S,D_{CORR}} )} = {\sqrt{R_{OLD}^{2} - \rho^{2}} - \sqrt{( \frac{R_{OLD}( {n - 1} )}{n - 1 + {R_{OLD}D_{CORR}}} )^{2} - \rho^{2}} - \sqrt{R_{OLD}^{2} - \frac{S^{2}}{4}} + \sqrt{( \frac{R_{OLD}( {n - 1} )}{n - 1 + {R_{OLD}D_{CORR}}} )^{2} - \frac{S^{2}}{4}}}$

The myopic ablation function MYO_ABLATE returns a needed depth ofablation at a particular distance ρ from the axis of treatment 102,given the uncorrected radius of curvature of the eye 44 R_(OLD), adesired zone of correction S, and a desired degree of correctionD_(CORR). The function MYO_ABLATE also provides the appropriate degreeof correction across the width S of a trench used to correct forastigmatism, as illustrated in FIGS. 4A and 4B.

Turning to FIG. 7B, the formula for hyperopic ablation is given below:${{HYP\_ ABLATE}( {\rho,R_{OLD},D_{CORR}} )} = {\sqrt{R_{OLD}^{2} - \rho^{2}} - \sqrt{( \frac{R_{OLD}( {n - 1} )}{n - 1 + {R_{OLD}D_{CORR}}} )^{2} - \rho^{2}} + \frac{R_{OLD}( {n - 1} )}{n - 1 + {R_{OLD}D_{CORR}}} - R_{01}}$

The hyperopia ablate function HYP_ABLATE only uses three parameters, asit does not need optical zone of correction S.

These specific algorithms for creating appropriate curvatures are wellknown in the art and can be found in MUNNERLYN, C. AND KOONS, S.,PHOTOREFRACTIVE KERATCTOMY: A TECHNIQUE FOR LASER REFRACTIVE SURGERY,Cataract Refract Surg., Vol. 14, (January 1988).

Further, in the routines for performing ablation discussed below inconjunction with FIGS. 9-14, the inverse of these equations are needed.While the above equations return a depth of ablation needed at aparticular value of ρ for a given degree of correction, the inverseequations do the exact opposite. They return the particular value of ρat which a particular depth of ablation is needed given a particulardegree of correction. These equations are given below:${{INV\_ MYO}{\_ ABLATE}( {R_{OLD},S,A,D_{CORR}} )} = {{{2( {R_{OLD}^{2} + R_{NEW}^{2}} )} - ( {C - A} )^{2} - {( \frac{R_{OLD}^{2} - R_{NEW}^{2}}{C - A} )^{2}\quad {where}\quad C}} = {{\sqrt{R_{NEW}^{2} - ( {S/2} )^{2}} - {\sqrt{R_{OLD}^{2} - ( {S/2} )^{2}}\quad {and}\quad R_{NEW}}} = {{NEW\_ RADIUS}( {R_{{OLD}^{\prime}}D_{CORR}} )}}}$${{INV\_ HYP}{\_ ABLATE}( {R_{OLD},A,D_{CORR}} )} = {{{2( {R_{OLD}^{2} + R_{NEW}^{2}} )} - ( {C - A} )^{2} - {( \frac{R_{OLD}^{2} - R_{NEW}^{2}}{C - A} )^{2}\quad {where}\quad C}} = {{R_{NEW} - {R_{OLD}\quad {and}\quad R_{NEW}}} = {{NEW\_ RADIUS}( {R_{{OLD}^{\prime}}D_{CORR}} )}}}$

The inverse myopic ablation function INV_MYO_ABLATE returns a parameterindicating the distance corresponding to ρ from the center of ablationin meters given a depth of ablation A, also in meters. It also uses theparameters R_(OLD), S, and The inverse hyperopic ablation functionINV_HYP_ABLATE also returns a radius from the center of ablation inmeters corresponding to ρ, given a depth of ablation A at a certaincorrection D_(CORR). It returns ρ indicating how far away from thecenter of ablation a certain depth of ablation will be found.

FIG. 8 illustrates how the system using aiming of the axis of ablationand variable spot sizes can correct for any topography of the eye 44that is abnormal, including non-symmetric topographies. In FIG. 8, oneline of a desired treatment topography 190 is illustrated. This could beretrieved, for example, from a computerized eye topography system whichindicates various abnormalities in the surface of the eye 44. Using sucha topography system, the eye surgery system 10, using the control unit64, then performs a series of shots, which, for simplicity, areillustrated as eight shots 192 through 206. In actual practice, a fargreater number of shots would likely be used. As the system knows theneeded ablation at each point, it creates a map of the topographydesired and performs ablation using various shot sizes aimed at variouspoints to perform the necessary correction. In this way, a wide varietyof non-symmetrical defects of the cornea can be corrected, such as appleand banana shapes, as well as any other abnormal shape.

FIG. 9 is a flowchart illustrating a CALCULATE routine 700 that wouldexecute preferably on the control unit 64. The CALCULATE routine 700calculates a series of shot patterns necessary to perform the desiredablation of the eye 44 to correct for a variety of conditions. In thedescribed embodiment, shot patterns are created to correct forastigmatism, hyperopia, and myopia as described in conjunction withpreceding FIGS. 2A to 7. Further, the dithering as illustrated in FIGS.3 and 4 is applied to myopic correction shot patterns.

Preferably, the CALCULATE routine 700 runs in the control unit 64, whichperforms the necessary shot calculations before beginning an ablationsequence. By having all the points precalculated, there is no delay incalculation, so each successive shot can be fired in rapid sequence, assoon as the excimer laser 20 is ready. This provides for quickertreatment times and less difficulty in having the patient center on anoptical fixation point.

Beginning at step 702, the CALCULATE routine 700 sets a variableSTART_DITHER to 1. This variable indicates the first ablation shot atwhich dithering is to begin, and is further discussed below. Note thatall of the ablation shots are preferably stored in an array, andSTART_DITHER indicates a location within that array. Control proceedsfrom step 702 to step 704, where the routine 700 determines whetherastigmatism correction is desired. This is pre-entered by the physician,including both angle of and degree of astigmatic correction, along withthe maximum treatment area. As is readily apparent, the routine 700could also request a degree of curvature for the line of astigmaticcorrection in the case of non-symmetric astigmatism, and even providefor greater correction towards one or the other ends of the astigmaticregion.

If astigmatic correction is desired, control proceeds from step 704 tostep 706, where an ASTIGMATISM routine 750 is performed (discussed belowin conjunction with FIG. 10), creating the appropriate shot patterns forthe desired astigmatic correction. These shot patterns, for example,correspond to those discussed in conjunction with FIGS. 4A and 4B.

Once the shot pattern for astigmatic correction is calculated at step706, control proceeds to step 708, where START_DITHER is set to avariable LAST_VECTOR. LAST_VECTOR points to the last calculated shot inthe array for an ablation run. In this case, it points to the lastvector calculated by the ASTIGMATISM routine 750 (FIG. 10A). Becauseastigmatism involves overlapping shots rather than potentiallyreinforcing shots, dithering is preferably not performed duringastigmatism correction in the disclosed embodiment, although it couldbe.

From step 704, if no correction for astigmatism was desired, and fromstep 708 in any case, control then proceeds to step 710, where theCALCULATE routine 700 determines whether correction for myopia isdesired. If not, correction for hyperopia is desired, so controlproceeds to step 712 where a HYPEROPIA routine 850 is performed, to bediscussed below in conjunction with FIG. 12. As correction for hyperopiais similar to correction for astigmatism, but with the shots in a circlerather than a line, dithering is preferably not performed (although itcould be) in the disclosed embodiment, so control then proceeds to step714, where the routine 700 returns to a master routine, which thenallows the physician to begin execution of the shot sequence calculatedby the CALCULATE routine 700.

If at step 710 it was determined that correction for myopia is desired,the CALCULATE routine 700 then proceeds to step 716, where it determineswhether transition zones are requested. If so, multiple myopic shotseries must be formed with the initial “transition zone” series beingcreated by performing a myopia correction. This was discussed above inconjunction with FIG. 2B. So, control proceeds to step 718 where aMYOPIA routine is performed to create a transition zone. This creates astandard myopia correction shot sequence for the transition zone.

Proceeding again to step 716, it is again determined whether moretransition zones are required. If the last transition zone shot sequencehas been calculated, or if none is needed, control then proceeds to step720, where the MYOPIA routine is again executed, this time to providethe final correction for myopia.

The creation of series of shot sequences to correct for myopia is wellknown in the art. Given the necessary depth of ablation as determined bythe MYO_ABLATE function described above, a shot pattern is created usingappropriate shot sizes to conform to the necessary depth of ablation ateach point radiating away from the axis of treatment 102.

Control then proceeds to step 722, where a DITHER routine 940 or 970 isexecuted as described below in conjunction with FIGS. 13 and 14,performing dithering, or randomizing, on all shots from START_DITHER asset in either step 702 or step 708 to LAST_VECTOR, which was describedabove in conjunction with step 708. At this point, calculation of theablation shot sequence is complete, so control proceeds to step 714where the CALCULATE routine 700 returns to the main program so that thephysician can execute the ablation run as is now stored in the array.

FIG. 10 is a flowchart of the ASTIGMATISM routine 750 that is used tocalculate the shot vectors necessary to create “trenches” of overlappinglines to correct for a desired dioptric degree of astigmatism along aparticular axis. An appropriate number of trenches is created, with eachtrench preferably using progressively larger spot sizes. Beginning atstep 752, the necessary depth of overall ablation is calculated at thedeepest part of the series of trenches. This is done using the myopicablation function MYO_ABLATE, described above in conjunction with FIG.7A. A variable MAX_ABLATE is set to the value returned by MYO_ABLATEusing ρ=0, indicating the necessary depth at the center of the trench(the deepest point). Also passed to MYO_ABLATE are the uncorrectedradius of curvature R_(OLD), the necessary dioptric correction D_(CORR),and the width of the astigmatism treatment zone S. Note that S is equalto the width of the astigmatism treatment zone, not the length.

Control then proceeds to step 754, where the necessary depth of ablationper trench is calculated. This is preferably calculated as is MAX_ABLATEabove, but instead setting a variable ABLATE, which indicates the amountof ablation per trench, to a value equal to MAX_ABLATE divided by 10.This indicates that preferably ten trenches are to be made, althoughless may be required as the amount of ablation per trench is calculated.

Control then proceeds to step 756, where a variable DEPTH is set equalto the previously calculated MAX_ABLATE minus ABLATE. DEPTH indicatesthe amount of ablation remaining to be performed to provide the desireddegree of correction.

Control then proceeds to step 758, where a minimum spot diameterMIN_SPOT_DIAM is calculated, indicating the smallest spot diameter to beused to create a trench. MIN_SPOT_DIAM is set equal to two times theradius returned by the inverted myopic ablation function INV_MYO_ABLATE.INV_MYO_ABLATE is called with the initial radius of curvature R_(OLD),with A set to DEPTH plus ABLATE/2, with D_(CORR) as the degree ofdioptric correction desired, and with S as the width of the treatmentzone. The value returned by calling this function is the radius at which95% of the overall ablation depth needed will be performed, and thisradius will preferably be relatively close to the center of the axis oftreatment—i.e., the radius will be small compared to the overall widthof each trench.

Proceeding to step 760, a maximum spot diameter MAX_SPOT_DIAM is setequal to S, which is simply the width of the astigmatism treatment zone100 (not the length).

Proceeding to step 762, a loop is entered that creates a series oftrenches to provide for the overall degree of correction for astigmatismneeded. First, at step 762 it is determined whether DEPTH is greaterthan zero. Again, DEPTH is the remaining depth necessary to ablate,which will be greater than zero when enough trenches have not beencreated to provide the desired degree of correction.

If DEPTH is greater than zero, control proceeds to step 764, where thespot diameter SPOT_DIAM is set equal to two times the result returned byINV_MYO_ABLATE, when that function is called with A set equal to DEPTH.This returns the radius at which the ultimate necessary ablation equalsDEPTH. As DEPTH is initially nearly equal to the overall depth ofablation needed, the initial spot diameter will thus be small.

Proceeding to step 766, the spot diameter SPOT_DIAM is empiricallycorrected. This is done by setting SPOT_DIAM equal to(1+(0.3·SIN(π·(SPOT_DIAM−MIN_SPOT_DIAM)/(MAX_SPOT_DIAM−MIN_SPOT_DIAM)))).This performs an empirical adjustment to the spot diameter to providebetter results and better conform the overall correction to the desiredcurve necessary to correct for astigmatism.

Proceeding to step 768, a variable STEP indicating the amount to movethe spot target on each succeeding shot is set equal toSPOT_DIAM·(DEPTH_PER_SHOT/ABLATE). DEPTH_PER_SHOT is the amount ofablation per shot, and is typically 0.2 μm. Then, at step 770 a variableOVERLAP is set equal to 100·(SPOT_DIAM−STEP)/SPOT_DIAM. This is theamount of overlap in percent needed for each shot.

Proceeding to step 772, a routine LINE 800 is called, discussed below inconjunction with FIG. 11, with Θ set to the angle at which to create theline of astigmatism, a LENGTH variable set to a predetermined length ofthe astigmatism series of shots plus 2·SPOT_DIAM, SPOT_DIAM indicatingthe spot size, and OVERLAP.

The series of shots for the line having been created, control proceedsto 774, where DEPTH is reduced by ABLATE, which is the amount to ablateper trench. Control then loops to step 762, where the reduced value ofDEPTH is again compared to zero. This loop is repeated, creating linesof shots with progressively larger spot diameters, until DEPTH is lessthan zero. DEPTH will be less than zero when virtually all of theablation shots have been calculated necessary to perform the desireddegree of correction.

Once DEPTH is less than zero, control proceeds to step 776 (FIG. 10B),where it is determined whether DEPTH plus ABLATE is greater thanDEPTH_PER_SHOT. If not, then another line of ablation should not beperformed, as that would provide too much correction, so control thenproceeds to step 778 where the ASTIGMATISM routine 750 returns to theCORRECTION routine 700.

If at step 776 the “residue” of ablation still needed does not exceedDEPTH_PER_SHOT, control instead proceeds to step 780. There, SPOT_DIAMis set to the maximum spot diameter of S, which is the width of thetreatment zone 100 for the astigmatism line of trenches, STEP is setequal to SPOT_DIAM·DEPTH_PER_SHOT/(ABLATE+DEPTH) and OVERLAP is setequal to (SPOT_DIAM−STEP)·100/SPOT_DIAM.

Control then proceeds to step 782, where a final trench is created usingthe variables set at step 780 spot width by calling the routine LINE800. The routine 750 then returns at step 778.

The ASTIGMATISM routine 750 thus creates a shot pattern as describedabove in conjunction with FIG. 4A.

FIG. 11 is a flowchart of the LINE routine 800. This routine 800calculates the shots for the generation of a line used in creating anastigmatism correction sequence of shots. The desired spot size ispassed to the routine 800 in a variable SPOT_DIAM, an overlap percentageis passed in a variable OVERLAP, and the length of the line isdetermined by a LENGTH variable passed to the LINE routine 800.

Beginning at step 802, the LINE routine 800 first calculates the stepsize, which is equal to SPOT_DIAM·(1−OVERLAP). Proceeding to step 804,the number of shots required is calculated equal to the truncated valueof (LENGTH−SPOT_DIAM+STEP)/STEP. Proceeding to step 806, a countervariable I is set equal to a variable START_VECTOR which is equal toLAST_VECTOR+1. LAST_VECTOR is set equal to I upon completion of the LINEroutine 800.

Control then proceeds to step 808, where a variable corresponding to theX axis displacement from the axis of treatment 102 is set equal to((LENGTH−SPOT_DIAM)/2)·cos θ, where θ is the angle of desired astigmaticcorrection. In step 810, Y is correspondingly set to((LENGTH−SPOT_DIAM)/2)·sin θ.

Control then proceeds to step 812, where it is determined whether Iequals START_VECTOR plus SHOTS, indicating the end of this line ofshots. If not, control proceeds to step 814, where an array locationX_SHOT[I] corresponding to the shot location of this particular shot isset equal to X and Y_SHOT[I] is correspondingly set equal to I. Then, atstep 816 X is set equal to X+(STEP·cos θ) and Y is set equal toY+(STEP·sin θ). This is the delta increment required for the next shot.

Control then proceeds to step 818, where I is incremented, and theroutine then loops to step 812. Once I is equal to START_VECTOR+SHOTS,indicating the end of this line, the routine returns to the ASTIGMATISMroutine 750 at step 820.

FIG. 12 is a flowchart of the HYPEROPIA routine 850 that createscircular trenches about the axis of treatment 102. It is similar to theASTIGMATISM routine 750, but creates the circular trenches of anappropriate profile to correct for hyperopia rather than for astigmatism(which uses a myopia correction function).

Beginning at step 852, a variable DEPTH is set equal to the parameterreturned by HYP_ABLATE discussed above in conjunction with FIG. 7B, whenρ is set equal to S/2−MIN_SPOT_RADIUS, where S is the diameter of theappropriate area of treatment and MIN_SPOT_RADIUS is the minimum spotsize to ever be used for hyperopia ablation, which could be set, forexample to 200 μm. HYP_ABLATE is also called with R_(OLD) representingthe uncorrected curvature of the eye 44 and D representing the desireddegree of dioptric correction. DEPTH thus equals the remaining depth toablate. It is initially less than the total depth to ablate, as ρ wasset just inside the circle of ablation as indicated by S/2 withMIN_SPOT_RADIUS subtracted, which is the first spot radius at which toablate.

Proceeding to step 854, a variable ABLATE, which indicates the amount toablate for this hyperopia treatment, is set equal to a parameterreturned by HYP_ABLATE called with ρ equal to S/2, with that returnedparameter decreased by the amount DEPTH. Thus, ABLATE is the differencein depth at the edge of the area of treatment as indicated by S/2 andthe depth at a distance MIN_SPOT_RADIUS just inside that treatment area.

Proceeding to step 856, a variable SPOT_DIAM is set equal toMIN_SPOT_RADIUS·2, a variable STEP is set equal toSPOT_DIAM·DEPTH_PER_SHOT/ABLATE, and a variable OVERLAP is set equal to((SPOT_DIAM−STEP)/SPOT_DIAM)·100 (i.e., expressed as percent). Thus, thefirst circular trench will be shot using the minimum spot diameter asindicated by MIN_SPOT_RADIUS·2.

Proceeding to step 858, a routine CIRCLE_LINE is called which calculatesthe series of shots necessary to ablate a circular trench given thevariables SPOT_DIAM, STEP, and OVERLAP. The CIRCLE_LINE routine directlycorresponds to the LINE routine 800, except that the circle is shot at afixed radius given by S/2, instead of being shot along a line. Itsimplementation corresponds to the LINE routine 800, with the exceptionthat each succeeding shot is incremented along the radius of ρ equal toS/2, rather than along a line.

Proceeding to step 860, ABLATE is set equal to a parameter returned byHYP_ABLATE when HYP_ABLATE is called with ρ equal to S/2, with thatreturned parameter then divided by 10. This corresponds to preferablyten trenches being ablated to form the appropriate profile of curvatureto correct for hyperopia.

Proceeding to 862, DEPTH is then set to DEPTH minus ABLATE, whichreduces DEPTH by {fraction (1/10)}th of the total depth needed to ablatethe hyperopic trench.

The routine 850 then proceeds to step 864, where it is determinedwhether DEPTH, which indicates the total depth remaining to ablate, isgreater than zero. If so, then there remaining trenches to ablate, sothe routine proceeds to step 866, where SPOT_DIAM is set equal to theparameter returned by INV_HYP_ABLATE when that function is called with Aequal to DEPTH. This then returns the radius at which ablation mustoccur to a depth equal to the current value of DEPTH in order to providethe appropriate correction for hyperopia. This returned parameter,however, is a radius from the axis of treatment 102. To calculate theactual spot diameter, SPOT_DIAM is set equal to 2·(S/2−SPOT_DIAM). Thissets SPOT_DIAM to two times the difference of the radius of the actualzone of treatment minus the radius at which the current ablation depthis to occur. This difference in radii times two is thus equal to thespot diameter for the current trench to ablate.

Proceeding to step 868, STEP is set equal toSPOT_DIAM·DEPTH_PER_SHOT/ABLATE. Proceeding to step 870, OVERLAP is setequal to ((SPOT_DIAM−STEP)/SPOT_DIAM)·100, which sets the appropriateoverlap in percent.

Using these values of SPOT_DIAM and OVERLAP, and with ρ equal to S/2, atstep 872 the routine CIRCLE LINE is called, creating a circular trench.Proceeding to step 874, DEPTH is again set equal to DEPTH minus ABLATE.The routine then loops to step 864, and continually loops through steps866 through 874 until DEPTH is not greater than zero.

When DEPTH is not greater than zero at step 864, the routine 850proceeds to step 876, where it is determined whether ABLATE plus DEPTHis greater than RESIDUE, where RESIDUE is an arbitrary value at whichanother trench is not to be ablated. This value is preferably 500microns, although could be a different value. If ABLATE plus DEPTH isgreater than RESIDUE, then more than that RESIDUE value remains to beablated, so the routine 850 proceeds to step 878, where a final trenchis created using a SPOT_DIAM of 2·(S/2−MIN_SPOT_SIZE) and an OVERLAP of((SPOT_DIAM−STEP)/SPOT_DIAM)·100. Then from step 876 and step 878, theroutine returns at step 880.

FIG. 13 is a flowchart of a RAND_DITHER routine 940 which corresponds tothe DITHER routine as noted in step 722 of FIG. 9. The RAND_DITHERroutine 940 randomly dithers all vectors in the described array fromSTART_DITH to LAST_VECTOR. START_DITH was previously set at step 702 orstep 708 of FIG. 9 to be equal to the first array location followingshots used for correction of astigmatism. Thus, dithering is preferablyapplied to the myopia correction, rather than to the astigmatismcorrection. The RAND_DITH routine 970 creates a shot pattern as isillustrated in FIG. 3A.

The RAND_DITHER routine 940 begins at step 942 by setting a countervariable I to START_DITH. Control then proceeds to step 944, where anintermediate variable X_DUM is set equal to a random number RANDOMbetween −0.5 and 0.5 times AMPLITUDE times SPOT_SIZE[I]. The variableAMPLITUDE was passed to the RAND_DITHER routine 940 as indicating theappropriate amplitude of dithering in fractional percentage of spotsize, and SPOT_SIZE[I] corresponds to the spot size for this particularshot.

Control then proceeds to step 946, where the routine 940 determineswhether the absolute value of X_DUM is greater than a limiting sizedenoted by a variable LIMIT, which is predetermined by the system. IfX_DUM is too large, control then proceeds to step 948, where X_DUM isset equal to LIMIT X_DUM/ABS(X_DUM), which sets X_DUM to LIMIT with theappropriate sign appended.

If X_DUM was not too large in step 946, and in any case from step 948,control then proceeds to step 950, where X_SHOT[I] is set equal toX_SHOT[I]+X_DUM, which provides a random dithering effect according tothe invention. Control then proceeds to steps 952, 954, 956, and 958,where Y_SHOT[I] is adjusted with the random dithering as X_SHOT[I] wasdithered at steps 944 through 950.

Control then proceeds from step 958 to step 960, where the RAND_DITHERroutine 940 determines if I=LAST_VECTOR, indicating that the last vectordesired has been dithered. If not, control proceeds to step 962, where Iis incremented, and control then loops to step 944 to process the nextshot.

If at step 960 I equals LAST_VECTOR, the RAND_DITHER routine 940 iscomplete, so the routine 940 then returns at step 964.

FIG. 19 shows an alternative routine CIRCLE_DITH 970, which can be usedinstead of the RAND_DITH routine 940. A shot pattern as created by theCIRCLE_DITH routine 970 is illustrated in FIG. 3B. The CIRCLE_DITHroutine 970 begins at step 972, where a variable NUM_VECT is setLAST_VECTOR-START_VECTOR, both of which were passed by the callingroutine. Proceeding to step 974, it is determined whetherNUM_VECT/ROTATIONS is less than 10. The variable ROTATIONS is passed tothe routine 970 to indicate how many circular rotations to make aroundthe axis of treatment 102 in adjusting all of the shots. The check ismade at 974 to prevent an excessive number of rotations if there areinsufficient shots. For example, if there are only twenty vectors, tenrevolutions would result in two sets of ten shots each 180° apart. Byarbitrarily requiring NUM_VECT/ROTATIONS to be at least 10, thisprevents such accumulation of shots, requiring the shots be distributedover at least ten different points around the axis of treatment 102. IfNUM_VECT/ROTATIONS is less than 10, control proceeds to step 976, whereROTATIONS is set equal to the truncated value of NUM_VECT/10. From step976 and 974, if that step was not true, control then proceeds to step978, where I is set equal to START_VECTOR.

Control then proceeds to step 980, where X_SHOT[I] is set equal toX_SHOT[I]+(DIAM/2)·cos((2π·I·ROTATIONS)/NUM_VECT). This circularlyadjusts the center of each shot. Y_SHOT[I] is correspondingly adjustedin step 982.

From step 982, control proceeds to step 984, where it is determinedwhether I is equal to LAST_VECTOR. If not, control then proceeds to step986 where I is incremented for another pass through steps 980 and 982 toadjust subsequent vectors.

If from step 984 I is equal to LAST_VECTOR, control then proceeds tostep 988, where control returns to the CALCULATE routine 700.

It will be readily appreciated that this dithering, or oscillation,could also be applied one dimensionally, and could be used for hyperopiaand astigmatism correction as well.

FIG. 15 illustrates an image returned by the video unit 56 in performingepithelia ablation using infrared dye and using the scanning large beamaccording to the invention. The epithelium is typically approximately 50μm thick. As the preferred excimer laser 20 used in the system Saccording to the invention ablates approximately 0.2 μm per shot, 250initial shots will typically be needed until the epithelium has beenablated. At some time before that point, however, variations of theepithelia thickness come into play. For example, some points might be 40μm thick, while others are 60 μm thick.

The system S according to the invention removes the epithelium bysensing when it has completely removed at least a portion of theepithelium, and then selectively removing the remainder. FIG. 15illustrates an epithelial removal zone 1000 in which a predeterminednumber of shots have been previously performed using a spot size thesize of the epithelial removal region 1000. After each shot, theinfrared video unit 56 captures any infrared fluorescence emitted fromthe eye 44. This fluorescence is created by first dyeing the epitheliumwith an infrared fluorescent dye that does not dye the layers underlyingthe epithelium. This dye is preferably infrared fluorescent to reducethe possibility of a pumped lasing action into the eye 44 of damagingfrequencies of light at damaging energies. Other dyes could be used,including visible light emitting dyes, if it is ensured that no pumpedlasing action will occur that might damage the eye 44. Infraredfluorescent dye is also preferred to prevent any distracting opticalaffects to the patient while the epithelium is being ablated.

After a predetermined number of shots, the video unit 56 will detectsome portion of the epithelial removal region 1000 that does notfluoresce. This indicates that there is no infrared fluorescent dye atthat location, which correspondingly indicates the epithelium has beenentirely ablated at that point.

In FIG. 15, two regions 1002 and 1004 are shown in which all of theepithelium has been removed by the predetermined number of shots. Atthis point, the spot size is reduced, and a region 1006 in which theepithelium still remains, as indicated by the infrared fluorescent dye,is further ablated.

Either under computer control or under physician control, the selectiveablation is performed as illustrated in FIG. 16. In FIG. 16, theremaining region 1006 has been further ablated using reduced spot sizes,forming further epithelial free regions 1008, 1010, 1012, 1014, and1016. The video unit 56 further observes the epithelial removal region1000 during ablation of each of these remaining regions, detecting whena certain portion of those regions do not fluoresce. Again, differencesin epithelial depth across each of these regions can result in onlypartial ablation of the epithelium in these remaining regions. Forexample, an island 1018 of epithelium is shown remaining in the region1008 which has been further ablated. Such islands must be furtherablated, along with any remaining portion of the epithelium 1006 whichhas not been removed by the subsequent ablation.

It will be recognized that by keeping a computer map of the epithelialremoval region 1000, along with the number of shots fired onto eachparticular point in that region, a map of epithelial thickness can becreated. By knowing the ablation depth of each shot, along with whereeach shot has been fired, it is known how many shots a particular pointreceives before all of the epithelium is removed from that region. Thus,a map of the thickness of the epithelium is created. This map would besimilar to that created in correcting for non-symmetrical opticalaberrations as discussed in conjunction with FIG. 8.

It will be appreciated that the large beam scanning and ditheringaccording to the invention need not only be applied to the surface ofthe eye 44. For example, U.S. Pat. No. 4,903,695, entitled “Method andApparatus for Performing a Keratomileusis or the Like Operation,” issuedFeb. 27, 1990, discloses a method of removing a portion of the corneafrom the eye and then ablating the exposed surface. Thus, the method andapparatus according to the invention can also be used on the exposedsurface resulting from such a keratomileusis type procedure. In such acase, the axis of treatment 102 would fall either on either the severedportion of the cornea or on the surface of the cornea from which aportion had been severed.

The foregoing disclosure and description of the invention areillustrative and explanatory thereof, and various changes in the size,shape, materials, components, circuit elements, and optical components,as well as in the details of the illustrated system and construction andmethod of operation may be made without departing from the spirit of theinvention.

What is claimed is:
 1. An eye surgery system for shaping the cornea ofthe eye, comprising: a laser that emits a light beam having apropagation axis; an optical system cooperating with the laser thatdirects the light beam to the cornea forming a light spot on a surfaceof the cornea, wherein the propagation axis of the light beam at thecornea locates the position of the light spot on the corneal surface;and a control unit in cooperation with the optical system that controlsa light spot sizing component of the optical system to create aselectively variable size of the light spot on the corneal surface and apropagation axis directing component of the optical system for locatingthe beam spot at a selective plurality of locations on the cornealsurface, wherein the control unit regulates the size of the light spotin correlation to the selective directing of the beam propagation axis.2. The eye surgery system of claim 1, wherein a maximum size of thelight spot on the cornea is limited by the control unit to a light spotarea between approximately 10% and approximately 90% of a totaltreatment area of a region of the cornea from which tissue is to beremoved to achieve a desired vision correction profile.
 3. The eyesurgery system of claim 2, wherein the maximum size of the light spotarea is between approximately 20% and approximately 80% of the totaltreatment area.
 4. The eye surgery system of claim 1, wherein themaximum size of the light spot is limited by the control unit in amanner that depends on the shape and the size of the region from whichtissue is to be removed.
 5. The eye surgery system of claim 1, whereinthe optical system comprises a scanning mirror that scans the spot overthe cornea.
 6. The eye surgery system of claim 5, wherein the controlunit is adapted to move the scanning mirror such that the light spot onthe cornea oscillates from shot to shot in at least one direction. 7.The eye surgery system of claim 5, wherein the scanning mirror has amotion that moves a propagatin axis of the light spot over aconic-shaped shell surface.
 8. The eye surgery system of claim 7,wherein the mirror motion produces a circular pattern of overlappingshots projected onto the eye.
 9. The eye surgery system of claim 7,wherein the optical system comprises a diaphragm located in an opticalpath of the beam that forms the light spot, further wherein thediaphragm produces a homogeneous energy distribution over the light spotarea deposited on the eye during movement of the axis of the light onthe conic-shaped shell surface.
 10. The eye surgery system of claim 9,wherein the diaphragm is rotatably mounted to rotate asynchronously withrespect to the movement of the axis of the light on the conic-shapedshell.
 11. The eye surgery system of claim 5, wherein the optical systemcomprises a diaphragm that forms the shape of the light spot, located ina optical path of the beam in a location before or after the scanningmirror.
 12. The eye surgery system of claim 11, wherein the diaphragmhas a controlled motion synchronous with the movement of the scanningmirror.
 13. The eye surgery system of claim 11, wherein the diaphragmhas a shape that produces a non-axially symmetric laser spot shape. 14.The eye surgery system of claim 5, wherein the scanning mirror can tiltabout at least one axis.
 15. The eye surgery system of claim 1, whereinthe laser is an excimer laser having a pulsed output beam.
 16. The eyesurgery system of claim 1, wherein the optical system comprises anadjustable diaphragm located in an optical path of the beam to allow foradjustment of a shape and an area of the beam spot, and furthercomprising a spot mode lens retractably positioned in the beam path toeffect one of a desired therapeutic treatment and a desired refractivetreatment.
 17. The eye surgery system of claim 1, wherein theselectively controlled light spot position generates a controlledaxisymmetric ablation profile.
 18. The system of claim 1, furthercomprising a second laser having a visible light beam propagationpathway at least partly coincident with the propagation axis of thelight beam.
 19. The system of claim 18, wherein the second laser lightbeam propagation pathway is centered on an axis of treatment of the eye.20. The system of claim 18, wherein the second laser emits a continuouswave laser beam.
 21. The system of claim 20, wherein the second laserbeam has a wavelength that does not ablate corneal tissue.
 22. Thesystem of claim 21, wherein the second laser beam wavelength is in thered part of the visible spectrum.
 23. The system of claim 18, furthercomprising a third laser having a visible light beam propagationpathway, said pathway having an impingement location on the eye that isthe same as an impingement location of the second laser beam propagationpathway.
 24. The system of claim 23, wherein the third laser emits acontinuous wave laser beam.
 25. The system of claim 23, wherein thethird laser beam has a wavelength that does not ablate corneal tissue.26. The system of claim 23, wherein the third laser beam has awavelength that is different than the wavelength of the second laser.27. The system of claim 23, wherein the third laser beam wavelength isin the green part of the visible spectrum.
 28. The system of claim 23,wherein the second laser and the third laser each provide a beam havinga power less than 1 mW.
 29. A method of shaping the cornea of the eye,the method comprising: providing laser light having a beam propagationaxis for removing eye tissue; forming a spot of the light on the cornea;and varying the size of the spot up to a maximum size having an areathat is smaller than a treatment area of the cornea and selectivelycontrolling a scanning position of the spot on the cornea relative to adesired treatment profile within the treatment area of the cornea,wherein the size of the spot is controlled in correlation with eachselectively controlled scanning position of the beam spot on the cornea.30. The method of claim 29, wherein the varying comprises limiting themaximum size to an area between approximately 10% and approximately 90%of the treatment area.
 31. The method of claim 29, wherein the varyingcomprises limiting the maximum size to an area between approximately 20%and approximately 80% of the treatment area.
 32. The method of claim 29,wherein the varying comprises limiting the maximum size in response tothe shape and size of the treatment area of the cornea.
 33. The methodof claim 29, further comprising physically moving the eye as an aid inproviding laser light shots at different locations on the eye.
 34. Themethod according to claim 29, further comprising providing a fixationpoint for a patient's eye with a visible laser light beam having apropagation path that is coincident with the laser beam propagationaxis.
 35. The method according claim 29, further comprising centeringthe laser light on a treatment axis of the eye with a visible lightlaser having a beam propagation path that is coincident with the laserbeam propagation axis.
 36. The method according to claim 35, furthercomprising adjusting a distance of the patient's eye from an eye surgerysystem by locating the eye at a point of intersection of the visiblelaser light and another visible laser light from a third laser with thecorneal surface.